Variable magnetic moment mr navigation

ABSTRACT

A method of navigating a medical device in an operating region in a subject. The method includes applying a magnetic field to the operating region and changing the magnetic moment of the medical device by selectively changing a physical condition of at least one magnet element in the medical device to change the orientation of the device with respect to the applied magnetic field.

CROSS REFERENCE TO RELATED APPLICATION

This application claims priority of prior provisional U.S. ApplicationSer. No. 60/467,683, filed May 2, 2004, the entire disclosure of whichis incorporated herein by reference.

BACKGROUND OF THE INVENTION

This invention relates to the navigation of medical devices in magneticfields, and in particular to the navigation of medical devices inmagnetic resonance imaging equipment.

The navigation of a medical device in an operating region with the aidof an externally applied magnetic field, such as that provided by an MRIdevice, by using a controllable variable magnetic moment in the devicetip has been proposed, and is in fact the subject of Kuhn, U.S. Pat. No.6,216,026, Arenson, U.S. Pat. No. 6,304,769, and Hastings et al., U.S.Pat. No. 6,401,723. One way of creating a controllable variable magneticmoment in a medical device disclosed in these patents is throughcontrolled variable currents in tiny coils in the distal end of thedevice, and preferably a set of at least three mutually perpendicularcoils. However, it can be expensive to fabricate such coils and assemblethem into the medical device. Furthermore, the magnetic field can causesignificant heating of the long electrical leads to the coils.

SUMMARY OF THE INVENTION

The present invention provides navigation in magnetic fields withreduced reliance upon, or even the complete elimination of microcoils,and their attendant problems. A preferred embodiment of a medical deviceconstructed according to the principles of this invention comprises atleast one element of a material whose magnetization can be altered bychanging a physical condition of the material. In accordance with themethod of this invention a magnetic field is applied to an operatingregion in the patient. The magnetic moment of the medical device isselectively changed by changing a physical condition of at least onemagnet element in the medical device to thereby change the orientationof the device with respect to the applied magnetic field.

In the preferred embodiment, the magnetic element has a Curietemperature in the range of normal body temperature, and themagnetization of the magnetic elements is controlled by raising andlowering the temperature of the magnetic element to selective reduce orincrease the magnetism of the elements. However, the magnetic elementscould be materials whose magnetism can be increased or decreased withother changes to the physical condition of the material, for examplepiezomagnetic materials whose magnetism changes with applied stress (orstrain); optimagetic materials whose magnetism changes with appliedlight; electri-magnetic materials whose magnetism changes with appliedelectrical field

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic diagram of a medical device constructed accordingto the principles of this invention;

FIG. 2 is a schematic diagram of a possible arrangement of sevenmagnetic elements, showing the elements with a maximum separation of60°;

FIG. 3 is a graph of the alignment torque on an iron rod versus fieldlead angle;

FIG. 4 is a graph of the torque on an iron rod versus applied magneticfield.

FIG. 5 is a schematic diagram of a curie element with thermal layer,heating (cooling) means, and thermocouple lead.;

FIG. 6 is a graph of the magnetization of Curie element sample in 0.5Tesla applied field;

FIG. 7 is a schematic drawing of a device constructed according to theprinciples of this invention;

FIG. 8 is a side elevation view of the distal tip of a medical deviceconstructed in accordance with the principles of this invention;

FIG. 9 is an enlarged side elevation view of the magnetic elements inthe distal tip of the medical device;

FIG. 10 is an enlarged end view of the magnetic elements in the distaltip of the medical device; and

FIG. 11 is an enlarged side elevation view of one set of the magneticelements in the distal tip of the medical device.

Corresponding reference numerals indicate corresponding parts throughoutthe several view of the drawings.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

A first embodiment of a medical device constructed according to theprinciples of this invention is indicated generally as 20 in FIG. 1. Asshown in FIG. 1, the medical device 20 has a proximal end 22 and adistal end 24. The device 20 includes at least one, and in thispreferred embodiment a plurality of, controllable magneticallyresponsive elements 26. One possible configuration of magneticallyresponsive elements 26 is shown in FIG. 2. As shown in FIG. 2, sevenelements 26 a-26 g are arranged in the distal end of the medical device,with a maximum angular spacing of 60°.

While variable current flowing in a coil generates a variable magneticmoment, various embodiments of the present invention can includealternate elements 26 to generate variable magnet moment to supplementor replace coils within a medical device. In some embodiments theelements 26 preferably reduce or eliminate the heat generated bymagnetic coils. In other embodiments the elements generate variablemagnetic moments without the need for electrical conductors to avoidelectrical heating of the electrical conductor lead wires by electricfields generated by the MRI imaging system.

There are a variety of materials whose magnetic properties can beselectively changed by changing a physical characteristic of thematerial for example by heating or cooling the material, by exposing thematerial to the light, or to an electric field. For example,thermomagnetic elements may be materials that have a Curie temperatureon the order of magnitude of body temperature. Stimulated variablemagnetization arises in materials due to alignment of atomic ormolecular spins and/or to long range order in a crystal lattice. Thesealignments or orderings can be interrupted or broken by externalstimuli, e.g. changes in physical condition. In a preferred embodiment,thermal stimulation or heating of the material reduces the magnetizationof the material. Specifically, each magnetic material has a “CurieTemperature”, T_(C), above which a given material is non-magnetic.Materials can be engineered to have a Curie Temperature in a desiredrange. If a material's T_(C) is somewhat higher than body temperature,then heating a material that resides within a catheter inside the bodywill reduce its magnetization. Similarly, if the material has a T_(C)somewhat lower than body temperature, magnetization is increased bycooling the material. In either case, variable temperature gives rise tovariable magnetic moment, which can be used to steer the catheter tip.

Opti-magnetic elements are materials whose magnetization can be alteredby exposure to light. Recent research has focused on transparent ortranslucent magnetic materials that have magnetization altered bypassing light of a given wavelength through the material. Such amaterial is discussed in Ohkoshi and Hashimoto, “New MagneticFunctionalities Presented by Prussian Blue Analogues”, in TheElectrochemical Society Interface, p. 34, (Fall 2002), incorporatedherein by reference. These or other opti-magnetic materials will allowsteering control through variable magnetic moments controlled by theapplication of varying light intensity supplied to the catheter tip,such as by fiber optic means.

Electri-magnetic materials are materials whose magnetization can bealtered by the application of an electric field. Alterations in crystalstructure can be induced in certain materials by the application of astatic electric field across the material. It may be anticipated thatmaterials may become available in which the application of a voltage(with little or no current), producing a DC electric field within thematerial, can enhance or reduce the material's magnetization.

Piezo-magnetic materials are materials whose magnetism can be altered bythe application of stress (or strain) to the material. The change ofmagnetic properties with the application of a stress or strain is knownas the Villari effect or the inverse magnetostriction effect or theinverse Joule effect. Stress or strain can be applied in a variety ofways, and can be either static or dynamic, the latter case including theacoustic application of force to the material (acousto-magnetic effect).

While variable current flowing in a coil generates a variable magneticmoment, alternate means are provided here to generate variable magneticmoment in materials contained within a device tip. An efficient meansfor moment variation that does not generate the heat associated withcurrents flowing in coils is needed. A preferred embodiment usesnon-electric current means to generate the variable moment, to avoidelectrical heating of the electrical conductor lead wires by rf electricfields generated by the MR imaging system. As disclosed herein avariable magnetic moment can be established in a medical device usingtemperature control of magnetic elements whose Curie temperature isclose to body temperature.

Thermo-Magnetic Elements

In a preferred embodiment, the elements 26 are permeable magneticmaterials near their T_(C). Above the Curie temperature, these materialsare non-magnetic. Below the Curie temperature, the magnetization of thematerial in an externally applied magnetic field increases astemperature decreases. In the strong magnetic fields of an MR imagingapparatus, the permeable material is saturated, and its saturationmagnetization increases with decreasing temperature to its asymptoticsaturation value. For ideal materials, the magnetization is about 80% ofits saturation value when its absolute temperature is about 80% of theCurie temperature. Specialty materials have been formulated for specificapplications that have much sharper Curie transitions (magnetizationrises sharply as temperature falls below T_(C)).

The plurality of elements 26 a-26 g are nominally held at a temperatureabove the Curie temperature, T_(C), so they are non-magnetic. During aninterventional procedure in an MRI machine, the catheter tip isdeflected by controllably reducing the temperature of one or moreelements below T_(C). Torques are exerted that tend to align theelements with the external MRI magnetic field. By controlling thetemperature of the individual elements comprising the tip, a net tipmagnetic moment is generated that can be oriented in any direction inspace to steer the catheter tip.

For materials that have T_(C) below body temperature, 37° C., theelements 26 are nominally non-magnetic. When it is desired to turn themedical device 20, one or more of the elements is cooled to atemperature below the Curie temperature to effect the turn. Since theelements are imaged in three dimensions by the MR imaging system, theproper element(s) 26 a-26 g can be selected for a turn specified by thephysician on the MR image. The physician can control the elementtemperature via a joy stick or other input device. Alternatively, thephysician can select the desired location or orientation of the tip, andthe computer can control the element temperatures and simultaneouslycontrol the catheter advancer to achieve the desired result. Cooling canbe achieved by passing an appropriate gas or liquid through a micro-tubewithin the catheter, exiting on or within the element. Gas exiting themicro-tube is cooled by expansion. A liquid that vaporizes upon exitingthe tube cools the element in addition by the heat of vaporization. Inaddition, the liquid or gas may be pre-cooled. Temperature is controlledby controlling the gas or liquid flow velocity. Individual elements maybe cooled by individual micro-tubes, or a single tube can be gated orswitched in the distal catheter tip to address a selected element. Apreferred element material with T_(C) below body temperature isgadolinium, with a Curie temperature of 19° C. Gadolinium shows up wellin an MR image, and is commonly used as a marker.

For materials that have T_(C) above body temperature, optical fibers maybe used to shine light on the elements to heat them above the Curiepoint. Nominally all elements would be heated above the Curie point.When it is desired to turn the medical device, heating is reduced to oneor more of the elements to achieve the desired movement of the devicetip. The temperature is controlled by controlling the light power. Afine wire thermocouple may be used to monitor and control temperature,however, a fiber optic micro-thermometer is preferred to avoid the needfor electrical leads.

Alternate heating and cooling means could be provided. Where electricallead wires are acceptable, or are made acceptable by shielding orinterruption of the rf E-field standing waves, electricalheating/cooling may be considered. Heating is readily achieved using aresistor, which may be constructed from fine wire. Alternatively,electrical current, either dc or ac may be passed through the elementitself, causing Ohmic heating within the element. In the latter case, itmay be desirable to construct the element from fine wire made from thematerial to increase its electrical resistance. Cooling is achievedelectrically with a Peltier-effect cooling chip.

In the above means, cooling is active and heating is passive (theelement absorbs heat from its surroundings), or vice versa. It will beshown below that the volume of material in an element required toprovide adequate catheter tip deflection is very small, and the amountof heat or energy required to raise or lower the element temperature istherefore very small. Therefore the element can be surrounded by a“leaky” thermal insulation layer adequate to avoid heating/cooling thesurrounding body tissues during element heating/cooling, yet whichconducts enough to allow the surrounding tissues to passively heat/coolthe element with a reasonable time constant. It is estimated later thatpassive heat/cool times of less than one second can be achieved.

Alternatively, active cooling can be used simultaneously with activeheating to achieve more rapid temperature control and thus rapidmagnetic response. Active heating and cooling could employ a combinationof fiber optic heaters and cooling fluid tubes. However, highefficiency, solid state, thermoelectric heater/coolers have becomeavailable and can be used to either heat or cool depending upon thedirection of current flow through these Peltier effect devices. Whilecurrent can be provided from a source outside the body throughelectrical lead wires, the use of laser energy, transmitted through thecatheter by fiber optic means, and converted to current in the cathetertip through thermoelectric or photoelectric elements is also possible.Appropriate micro-chips can be fabricated that contain the photovoltaiccell and Peltier effect elements. If a micro-chip controller isprovided, then a single fiber optic can be used to supply laser powerthat is converted to electrical energy in the catheter tip, which is inturn routed to the appropriate elements by the micro-controller. Aseparate optical communications fiber can be used to communicate withthe micro-controller, however, the main beam can consist of pulses thatare modulated to transfer data messages in addition to optical powerthrough a single fiber optic.

The volume and dimensions of the elements 26 necessary to achieve aspecified deflection angle of the medical device in an MRI magneticfield can be estimated for a given medical device. It is desirable thatthe deflection of medical devices in an MRI be comparable to thedeflection of a medical device in a dedicated magnetic navigationsystem, for example an EP mapping and ablation catheter being navigatedin a magnetic navigation system, such as the Niobe magnetic navigationsystem available from Stereotaxis, Inc., St. Louis, Mo. The elements 26should provide equivalent deflection to this catheter in the MR magneticfield. Thus, the maximum aligning torque on one of the elements 26 ispreferably at least equal to the maximum aligning torque of magneticcatheters in available magnetic navigation systems. The maximum aligningtorque on a magnet element on a magnetic catheter in a magneticnavigation system (MNS) and the maximum aligning torque on an element inan MRI may be expressed as:

τ_(max)=M_(catheter)B_(MNS)V_(EP)MNS  (1)

τ_(max) =M _(Curie) B _(MRI) V _(Curie)/√{square root over (2)}MRI  (2)

where M is the magnet magnetization, B is the applied field, and V isthe magnet volume. The square root of two appears in the second equationbecause the maximum torque occurs when the element is oriented 45degrees from the field direction (actually the peak is at a larger anglewhen the elements are saturated). Equating Eq. (1) and Eq. (2):

V _(Curie)=1.414*(M _(Catheter) /M _(Curie))*(B _(MNS) /B _(MRI))*V_(EP)  (3)

The measured magnetization of a Neo-45 catheter magnet is 1.2 Tesla,while a high quality permeable element (e.g., pure iron) can have asaturation magnetization of about 2 Tesla. The applied field in amagnetic navigation system is of the order of 0.1 Tesla, while it isexpected that MR interventions will take place in 3 Tesla MRI machinesto achieve image resolution adequate for navigation. Eq. (2) then gives:

V _(Curie) =V _(Catheter)/35  (4)

Equation 4 shows that the elements 26 in an MRI can yield the sametorque as the catheter magnet in a magnetic navigation system, but withabout 1/35^(th) the volume. This is important since multiple elementsmust be used to achieve omni-directional tip moment in a singledirection field. For a typical catheter magnet volume of 21.8 mm³, anelement volume of only 0.62 mm³ supplies the equivalent magnetic torquein an MRI.

The dimensions of a suitable element 26 can be can be determined fromthe fact that the diameter of a conventional magnetically navigablecatheter is about 2.5 mm (e.g., a magnetically guidable EP catheteravailable from Stereotaxis, Inc., St, Louis, Mo.). If the elements 26are arranged at an angle of 30° with respect to diameter of the device,the maximum length of the elements 26 is 2.9 mm. Given the desiredelement volume of 0.62 mm³, the element dimensions are preferably:

d=0.52 mm

L=2.9 mm

V=0.62 mm³

L/d=5.6  (5)

The L/d ratio for the element is important in calculating the torqueversus field angle function.

Permeable elements behave differently from permanent magnets in anexternal magnetic field. A permanent tip magnet will experience a torquethat tends to align the magnet with the external field. This torque isin the same direction for all “lead angles” (or angles between the tipmagnetic moment and applied field) between 0 and 180 degrees. Apermeable element however, has no intrinsic magnetization direction, andeither end of the element can align with a given pole of the externalfield. Thus the torque on an element is zero when the lead angle is 90degrees, because the element is torqued equally to the North and Southpoles of the applied field. The peak torque on an element in an MRIoccurs at a lead angle that depends upon the MRI element dimensions, andis about 70 degrees for the elements discussed above, decreasing rapidlyto zero at 90 degrees. In a given plane, multiple elements are requiredto achieve continuous torque in a given direction. At first blush, itwould appear that two elements are adequate in each of three orthogonalplanes to achieve omni-directional steering. However, the rapid drop intorque above 70 degrees lead angle means that a dead zone of angles willexist for two elements.

As shown in FIG. 2, at least one symmetrical arrangement of elementsexists in which three elements are placed in each of three planes withan angle of 60 degrees between planes. Pairs of elements may beactivated to achieve torques about any given axis.

The torque on the elements increases with the square of the appliedmagnetic field before the element saturates, and increases linearly withthe field thereafter. Below saturation, the peak torque occurs when thefield angle leads the element axis angle by 45°. As the elements becomemore saturated, the torque continues to increase somewhat above the 45°angle, and peaks closer to 90° when the elements are fully saturated.The torque then falls rapidly to zero at 90°, and reverses direction forangles larger than 90°. Since the elements will almost certainly besaturated in the 3 Tesla field of the MRI, peak torques will occurcloser to 90° lead angles. This is important for navigation. First,controlling torques over a larger range of angles than 0-45 degreesreduces requirements for image resolution and/or tip localizationaccuracy. Secondly, fewer elements are required, for example one elementevery 60 degrees instead of every 45 degrees for navigation, reducingthe total number of elements required from nine to seven.

Convenient, closed form, estimates for the element torque are givenbelow For closed form solutions, a simple two-branch model for theelement B-H curve is used:

B=μμ ₀ H, H<B _(S)/μμ₀

B=B _(S) , H<B _(S)/μμ₀  (6)

where μ is the element permeability, and B_(S) is the element saturationinduction. The torque on the element in an externally applied field isthen:

$\begin{matrix}{\tau = {\frac{\left( {V \cdot B^{2}} \right)}{2\; \mu_{0}}\left( {\lambda_{} - \lambda_{\bot}} \right){\sin \left( {2\; \theta} \right)}}} & (7)\end{matrix}$

where:

λ_(i)=γ_(i) when B<Bc

λ_(i)=γ_(i) B _(c) /B when B>B_(c)  (8)

where:

B _(c) =B _(s)(μ−1)/(μ√{square root over ((γ∥ cos(θ))²+(γ⊥sin(θ))²))}{square root over ((γ∥ cos(θ))²+(γ⊥ sin(θ))²))}

γ_(i)=(μ−1)/(1+(μ−1)β_(i))

where

-   -   τ=torque on the element in Nt-m    -   V=element volume in m³    -   B=magnitude of the applied magnetic field in Tesla    -   θ=angle between the element axis and the applied field, in        radians    -   β_(i)=demagnetizing factor parallel or perpendicular to the        element axis        The demagnetizing factors can be found in tables or derived from        formulas. They depend only upon the L/D ratio of the element.        Equation (7) is evaluated versus lead angle for various applied        fields in FIG. 4, and versus applied field for various lead        angles in FIG. 5. The values B_(S)=2 Tesla, and μ=20 appropriate        for iron were used in FIGS. 4 and 5, with element dimensions of        0.52 mm diameter by 3 mm length.

From FIG. 4 that the torque peaks at 45° lead angle in small fields, andpeaks at larger lead angles as the element becomes saturated in largerfields. FIG. 5 plots the torque on this element versus applied field forvarious lead angles. The maximum torque on a catheter magnet in amagnetic navigation system at 0.1 Tesla is shown for comparison. Atypical magnetic catheter tip magnet has magnetization of 1.2 Tesla andvolume of 21.8 mm³, yielding a maximum magnetic torque of 212 gm-mm in a0.1 Tesla applied field. For the element dimensions shown, the torque isequal to the catheter magnet torque at about 3 Tesla, as anticipated.

Heating and Cooling Times

To achieve navigation performance comparable to available magneticnavigation systems the elements must heat up and cool down in a fewseconds. For example, an element heated by an optical fiber terminatingat the center of the element (or a cooling tube in the sameconfiguration). FIG. 6 shows an element and surrounding thermal layerchosen to give proper cooling rates. A thermocouple (or fiber opticthermometer) is shown for temperature control.

The thermal diffusion time, or time for heat to be conducted from thecenter of the element to the end of the element is given by:

τ_(d)=(Cρ/κ)(L/2)²  (9)

where C is the element heat capacity, ρ is its density, and κ is thethermal conductivity. Some typical values for iron, nickel, and theiralloys are:

-   -   C≈0.1 cal/gm.° K.≈0.4 J/gm° K.    -   ρ≈8 gm./cm³    -   κ≈0.8 Watts/cm° K.    -   L=0.3 cm        giving:

τ_(d)≈0.1 seconds  (10)

which is shorter than some magnet navigation system response times. Thisassumes that the heat leak through the thermal layer is small comparedto the heating power.

For heated elements, the passive cooling time will depend upon thethermal conductivity of the thermal layer, which conducts heat throughits thickness from the hot element to the outside at body temperature.For cooling, the thermal diffusion time is given by:

τ_(c)=(Cρ/κ _(t))(Dt/4)  (11)

where κ_(t) is the thermal conductivity of the thermal layer, D is theelement diameter, and t is the thickness of the thermal layer. Picking athermal conductivity representative of insulating plastic materials, anda thickness of about 0.5 mm, which is close to the wall thickness of thecurrent magnetic catheter shaft, and D=0.5 mm. Evaluating Eq. (11)results in:

τ_(c)≈0.7 sec  (12)

where:

κ_(t)≈0.003 Watts/cm° K.

The heating input power required to heat the element to ΔT≈100° C. abovebody temperature in the thermal diffusion time of 0.1 second, and theheat loss through the thermal layer when the element is heated toΔT≈100° C. can be computed. The input power, neglecting the heat loss isgiven by:

P _(in) ≈CρVΔT/τ _(d)≈0.15 Joules/0.1 sec=1.5 Watts  (13)

and the heat loss through the thermal layer is:

P _(leak)=κ_(t) πDLΔT/t≈0.2 Watts  (14)

This verifies that the heat loss is small compared to the input power,and that the heat loss of 0.2 Watts will remove the stored heat energyin the element of about 0.15 Joules in about 0.7 seconds. The ratherlarge temperature rise of 100 degrees may not be required for some Curiematerials. A smaller ΔT will reduce the input and heat leak power butwill not change the heating and cooling times. Thus, it appears thatactive heating with passive cooling can control the elementmagnetization with an acceptably short time constant.

When active heating and cooling is employed, a very highly insulatingjacket can be used, and heat is applied and removed through thethermo-electric device, using a conductive material in contact withblood as the heat reservoir. The tiny heat of 0.15 Joules, required tochange the element temperature by 100° C., will not result in measurablechange the blood temperature of the patient. If this were a concern, aseparate heat reservoir could be supplied within the catheter tip, andthe entire catheter tip could then be thermally insulated. With activeheating/cooling, the catheter deflection response time would be on theorder of 0.1 seconds.

Several materials with Curie temperatures near body temperature havebeen identified. One likely candidate material that was tested isFe(74.1 wt %), Er(18.5 wt %), Dy(7.4 wt %). A small rectangular piece ofthis material was wrapped with a bi-filar heating coil and suspendedfrom a force gauge above a 12″×12″ permanent magnet in field of about0.5 Tesla. The sample was in a water bath at room temperature. Thesample magnetization was computed from the measured net magnetic forceand the known field gradient at the position of the sample, and wasfound to be approximately 1 Tesla. This nominal value is smaller thaniron, however, the magnetization value may be larger in a 3 T magneticfield. As is, the magnetization is large enough to be useful withslightly larger diameter elements. The force fell to zero as expectedwhen the sample was heated, as shown in FIG. 6. Heating and coolingtimes were measured, and found to be slightly larger than predicted fromEqs. (9) and (11).

Other suitable materials for use as Curie elements are Y₂Fe_(l7), HoFe,and Pd(94%)Co(6%). These materials have Curie temperatures in the range57° C. to 92° C., with a range of saturation magnetization values. Inaddition, Gadolinium (Gd) has a Curie temperature of 19° C., and isnon-magnetic at body temperature (37° C.). At −59° C. the absolutetemperature is 80% of the Curie absolute temperature, and most of thesaturation magnetization should be recovered at this temperature. Gd hasthe advantage that it is non-magnetic at room and body temperature goinginto the patient. Thus, zero cooling/heating power is required until thefirst steering move is commanded.

Thus, stimulated variable magnetization is possible, and in particularthe magnetic moment of a medical device can be controlled by controllingthe temperature of elements made of materials having Curie temperaturenear body temperature, and is feasible for steering catheters in an MRImachine.

An embodiment of a device constructed according to the principles ofthis invention and useful in the methods of this invention is indicatedgenerally as 100 in FIG. 7. The device 100 includes a magnetic element102, preferably made of a ferromagnetic material in the shape of acylinder. The magnetic characteristics of the material are selected fora desired Curie point and transition curve. One end of cylindricalmagnetic element 102 is mated to the end of an optical fiber 104. Energyin the form of laser radiation is deposited at this interface when thelaser is activated. The energy deposited raises the temperature of theelement at the interface with the fiber. This energy is quicklyconducted through the entire length of the element raising thetemperature of the entire element. When the laser radiation is no longerapplied, energy is lost from the seed through conduction into thesurrounding material and radiation in the form of IR. Some of this IR islost through the cylinder end that is mated to the optical fiber and canbe measured at the opposite end.

An optical fiber 104, consisting of a glass or polymer fiber (one ofmany in a multi-fiber bundle) that is used to transmit radiation fromone end of the fiber to the other with low transmission losses. One endof the fiber is mated to the end of the element 102 while the other isterminated at a beam splitter 106. The fiber 104 is used to transmitlight from a laser 108 to the magnet element 102 and IR from the elementsurface to an infrared thermometer 110.

The beam splitter 106 is a special lens that is used to break a beam oflight into two separate beams. This allows the light beam from the laser108 to be directed onto the optical fiber 104 where it is delivered tothe element 102. Returning IR from the element 102 is transmitted up theoptical fiber 104 and through the beam splitter 106 where it isredirected to the infrared thermometer 110.

The laser 108 provides the energy used to heat the element 102 in theform of light (or laser radiation) via the beam splitter 106 and opticalfiber 104. The operation of the laser 108 is cycled on and off atregular intervals with the length of the pulse during the “on cycle”determining the amount of energy deposited. Control of the cycling ofthe laser 108 is done by a dedicated switching controller 112.

The infrared thermometer 110 uses a sensor to measure IR radiation givenoff by a blackbody and converts it into a surface temperaturemeasurement. IR radiation is transmitted from the element 102 to thesensor via an optical fiber 104 and beam splitting lens 106 during the“off cycle” of the laser 108. From this measurement a value of surfacetemperature is generated and sent to the switching controller 112.

The switching controller 112 preferably consists of a micro-controllerboard and software control algorithm. The board has two inputs; thetemperature from the infrared thermometer 110 and a set-point valueprovided by an operator or external control device. The output of thedevice controls the on/off cycle of the laser 108. The control softwarecan use a PID algorithm to compare the input temperature to theset-point temperature, as well as the rate-of-change in the inputtemperature. From this a calculated value of how much energy needs to bedelivered during the next pulse is determined. The output of the board“cycles on” the laser 108 for a period of time necessary to deliver thecalculated amount of energy. Another set of data is collected from theinputs when the laser 108 is cycled off, and the process repeats.

In another embodiment, separate optical fibers may be used to deliverenergy to separate elements or sets of elements in the device. Theorientation of the device tip in three dimensions may be controlled byseparate heating or cooling of distinct elements or sets of elements, sothat the tip can be arbitrarily oriented in space. In this case theswitching controller 112 would also compute which elements to activateas well as their levels of activity, and appropriately direct energyinto the corresponding optical fiber(s).

An embodiment of a medical device in accordance with the presentinvention, and useful with the methods of the present invention isindicated generally as 200 in FIGS. 8 through 11. The device 200 ispreferably an elongate medical device, having a proximal end and adistal end 202. The medical device 200 could be a catheter, endoscope,or medical guide wire, or any other medical device that needs to benavigated within an operating region in a subject's body.

As shown in FIGS. 8-11 the device 200 comprises a plurality of magneticelements 204. These elements are preferably arranged so that they arecapable for creating a magnetic moment in any direction. As shown in theFigures, the elements 204 are arranged in three skewed, divergentcylindrical arrays of seven elements, comprising one generally axialelement, and six surrounding elements. These elements are spaced at 60°intervals around the axial element, and are canted at an angle of 60°relative to the axial direction. Of course some other arrangement ofelements 204 could be made. There are three arrays of elements toprovide more mass than a singe array, and but there could be fewer ormore arrays, if desired.

Each of the elements 204 is preferably made from a material having aCurie temperature that is in the range (i.e. within about 100° C.) ofnormal body temperature of 37° C. This range is desirable because thesetemperatures can be reached relatively quickly, and the heat can bedissipated relatively quickly, and it is relatively easy to shieldsurrounding body tissues from such temperatures. Examples of suitablematerials include Gadolinium (Gd) and Manganese Arsenide (MnAs). Eachelement 202 is generally cylindrical, and may have a diameter of 0.5 mmand a length of about 2.5 mm. While the Curie elements can beincorporated into medical devices of any diameter by selecting theappropriate element dimensions, it is important to maintain a ratio oflength to diameter for the elements that is large enough to provideadequate torque to the device. The torque on a sphere (length equaldiameter) is zero. Element 202 preferably has length equal to or greaterthan five times its diameter. Smaller ratios of length to diameter areacceptable, but require a larger element volume to achieve a givendesired torque.

A fiber optic lead 206 extends to each of the elements 204 forselectively conducting energy (light) to the element to heat it. Thefiber optic lead 206 may, for example, be seated in a recess in the endof the element 204. Of course, other methods can be used for heating theelements 204, for example small resistance heating elements, heatedfluid conductors, or Peltier heating/cooling elements. Electric currentcould also be applied directly to the elements 204 to heat them.

The fiber optic leads 206 may extend all the way to the proximal end ofthe device 200, or they may extend to a controller inside the device 200that is optically or electrically powered, and which either selectivelydistributes or selectively generates optical energy to the elements 204via leads 206, Control signals can be transmitted to the controller viaa separate electric, or preferably fiberoptic line, or the controlsignals can be transmitted over the electric or optic power line.

The elements 204 are preferably disposed in a hollow, generallycylindrical shell 208 at the distal end of the device 200. The shell 208may be made of platinum or a platinum-iridium alloy, or other suitablematerial. The shell is preferably sized and shaped, and made ofmaterials compatible with use in a magnetic field, and in particular themagnetic field of an MI imaging device. The shell 208 preferably has anoutside diameter of about 8 French (about 2.67 mm), and a length ofabout 6 mm.

In operation, the fiberoptic leads conduct sufficient light energy toall of the elements 204 so that the distal end of the device isnon-magnetic. The device 200 can be easily introduced into the operatingregion in a subject without interference from either the magnetic fieldof a magnetic surgery system or the magnetic field of an MR imagingsystem. When the user desires to change the orientation of the device200, the user can indicate the desired direction using an interface,which operates a computer controller to selectively interrupt thetransmission of energy to selected elements 204. As the selectedelements 204 cool, they regain the magnetism, creating a magnetic momentat the distal end of the device which interacts with the appliedmagnetic field (from either a magnetic surgery system or a MR imagingsystem) and changes the orientation of the distal end of the device.Because of the small size of the elements 204, they heat and coolrelatively rapidly, so that the device 200 can be navigated in realtime.

Some system for determining the location and/or orientation of thedevice is preferably provided to facilitate controllers identificationof the elements 204 to “turn on” by allowing them to cool.Alternatively, if the elements are constructed of a material with aCurie temperature below normal body temperature, the elements 204 arenormally off inside the body, and they are cooled to “turn on” ormagnetize the element.

The Curie Temperature is a measure of the temperature at which the slopeof the magnetization curve is a maximum, which for many materials isalso the temperature at which magnetism disappears. However, it is notnecessary to heat or cool materials to the Curie temperature foreffective magnetization. A sufficient decrease in magnetization in someelements may occur as the material is heated without reaching the Curietemperature, and, similarly, the elements may not have to be cooled tocompletely restore magnetization in order to effectively navigate.

The elements 204 can be manufactured as a unit, building up the elementsin their designed orientations in layers, using variousMicroelectromechanical System (MEMS) technologies, including for exampleEFAB marketing techniques available from MEMGen Corporation, Burbank,Calif. See, for example, Bang, EFAB, A New Approach to MEMS Fabrication.Sensors November 2002, and Judy et al., Magnetic Materials for MEMS,Jack W. Judy and Nosang Myung, “Magnetic Materials for MEMS”, MRSWorkshop on MEMS Materials, San Francisco, Calif., (Apr. 5-6, 2002), pp.23-26. These technologies will allow magnetic element arrays to beinexpensively fabricated in batch processes, in sizes that can beincorporated into endoscopes, catheters, and even into guidewires.

1.-32. (canceled)
 33. A medical device navigable in an operating regionin a subject using an externally applied magnetic field, the deviceincluding at least one element of a material whose magnetization can bealtered by changing a physical condition of the material.
 34. Themedical device according to claim 33 further comprising means forchanging the physical condition of the material.
 35. A medical devicenavigable in an operating region in a subject using an externallyapplied magnetic field, the device including at least one element of athermomagnetic material whose magnetization can be altered by atemperature change that is between 0° C. and 200° C.
 36. The medicaldevice according to claim 35 wherein the magnetization of thethermomagnetic material can be altered by a temperature change that iswithin 100° of body temperature.
 37. The medical device according toclaim 35 wherein the device includes an optomagnetic material whosemagnetization can be altered by the application of light.
 38. Themedical device according to claim 35 wherein the device includes anpiezomagnetic material whose magnetization can be altered by theapplication of pressure.
 39. The medical device according to claim 35wherein device includes an electri-magnetic element whose magnetizationdirection can be altered by the application of an electric field
 40. Themedical device according to claim 35 wherein the device includes anpiezomagnetic element whose magnetization direction can be altered bythe application of mechanical stress.
 41. The medical device accordingto claim 35 wherein the thermomagnetic material has a Curie temperatureabove normal body temperature, and further comprising means forselectively heating the at least one elements above the Curietemperature.
 42. The medical device according to claim 35 wherein thethermomagnetic material has a Curie temperature below normal bodytemperature, and further comprising means for selectively cooling the atleast one element below its Curie temperature.
 43. The medical deviceaccording to claim 35 wherein the plurality of elements are arranged inat least skewed, divergent cylindrical array. 44.-51. (canceled)
 52. Amedical device for navigation in an operating region in a subject towhich a magnetic field is applied, the device comprising means forchanging the magnetic moment at the distal end of the device.
 53. Amedical device for navigating in an operating region in a subject towhich a magnetic field is applied, the device comprising at least onemagnet element, and means for selectively changing a physical propertyof the at least one magnet element to change the magnetic moment of thedevice.
 54. The device according to claim 53 wherein in the means forselectively changing the physical property of the at least one magnetelement comprises means for heating the at least one magnet element. 55.The device according to claim 53 wherein in the means for selectivelychanging the physical property of the at least one magnet elementcomprises means for cooling the at least one magnet element.